System and method for transvascularly stimulating contents of the carotid sheath

ABSTRACT

Methods and systems are disclosed for stimulating contents of the carotid sheath using an intravascular pulse generator and lead. The lead carries an energy delivery device such as an electrode, which is anchor within the portion of the internal jugular vein that is disposed within the carotid sheath. The energy delivery device is energized to transvenously direct energy to target contents of the carotid sheath external to the internal jugular vein. Such target contents may include nervous system elements associated with the carotid sinus baroreceptors, the carotid sinus nerve and associated nerve branches, and or the vagus nerve and associated nerve branches. The system may be used to control blood pressure and/or to lower heart rate and may be suitable for treatment of hypertension, heart failure, or other conditions.

RELATED APPLICATIONS

This application is a continuation of U.S. Ser. No. 12/413,495, filedMar. 27, 2009, which claims the benefit of U.S. Provisional ApplicationNo. 61/039,793, filed Mar. 27, 2008, which is incorporated herein byreference.

FIELD OF THE INVENTION

The present invention generally relates to implantable devices andsystems, and associated methods for delivering therapy to nervestructures using components implanted within the vasculature.

BACKGROUND OF THE INVENTION

Heart failure (HF) is a condition characterized by reduced cardiacoutput that triggers neurohormonal activation. This compensatorymechanism functions acutely to increase cardiac output and restore leftventricular (LV) functional capacity such that patients remainasymptomatic. Over time, however, sustained activation of theseneurohormonal systems triggers pathologic LV remodeling and end-organdamage that ultimately drives the progression of HF.

In many people, persistent hypertension is the predominant contributingactor for development of HF. Management of hypertension can slow orprevent the natural evolution of HF.

The human body maintains blood pressure through the use of a centralcontrol mechanism located in the brain with numerous peripheral bloodpressure sensing components. These components are generally made ofspecialized cells embedded in the walls of blood vessels that createaction potentials at an increased rate as the cell is stretched. Thesegroups of cells are generally referred to as baroreceptors. The actionpotentials are propagated back to the central control center via neuralpathways along afferent nerves. While there are many baroreceptorcomponents located throughout the body, there are several that areparticularly important. Possibly the most important baroreceptor regionis located near the bifurcation of the common carotid artery into theinternal and external carotid. In this area there is a small enlargementof the vessel tissues, referred to as the carotid bulb or carotid sinus.The carotid baroreceptors are generally found throughout this area. Thecarotid baroreceptors and related neural pathways form the primarypressure sensing component that provides signals to the brain forregulating cranial and systemic blood pressure.

Applicant's prior Application Publication No. U.S. 2007/0255379, whichis incorporated herein by reference, discloses an intravascularneurostimulation device (such as a pulse generator) and associatedmethods for using the neurostimulation device to stimulate nervoussystem targets. As discussed in that application, targeting stimulationto baroreceptor afferents in HF patients can lead to decreases insympathetic tone, peripheral vascular resistance, and afterload. Suchstimulation can be used to control blood pressure as a treatment forhypertension or HF. Stimulation of the vagus nerve (e.g. vagalefferents) is known to cause a reduction in heart rate.

The present disclosure describes an implementation of Applicants'previously-disclosed intravascular systems and methods for use instimulating nervous system targets such as the vagus nerve and/or itsbranches, the carotid artery, the carotid sinus nerve and/or itsbranches, baroreceptors, and/or for otherwise activating a baroreceptorresponse. Systems and methods of the type disclosed may be used forcontrolling heart rate and/or regulating blood pressure for treatment ofhypertension, congestive heart failure or other conditions.

The internal jugular vein, vagus nerve, and common carotid artery (whichincludes the carotid sinus) are located within the carotid sheath, afascial compartment within the neck. The carotid sheath providesrelatively fixed geometric relationships between these structures whilealso giving some degree of insulation from surrounding tissue. Accordingto one embodiment disclosed herein, a method is disclosed fortransvascularly stimulating contents of the carotid sheath. The methodincludes advancing an energy delivery element, which may be anelectrode, into an internal jugular vein, retaining the energy deliveryelement in a portion of the internal jugular vein contained within acarotid sheath, and energizing the energy delivery element totransvenously direct energy to target contents of the carotid sheathexternal to the internal jugular vein. The energy may be directed to acarotid artery within the carotid sinus sheath, and/or to a carotidsinus nerve or nerve branch within the carotid sinus sheath, to nervebranches emanating from carotid artery baroreceptors, and/or to a vagusnerve or nerve branch within the carotid sinus sheath.

In some of the disclosed embodiments, a second electrode or other secondenergy delivery element is introduced into a second internal jugularvein and retained in a portion of the second internal jugular veincontained within a second carotid sheath. The second energy deliveryelement is energized to direct energy to contents of the second carotidsheath external to the second internal jugular vein.

Shielding may be used to minimize collateral stimulation of unintendedtargets. In one embodiment, a shield is positioned at least partiallysurrounding the carotid sinus sheath. The shield blocks conduction ofenergy beyond the sheath during energization of the energy deliveryelement. In another embodiment, an insulative material is delivered intoextravascular space adjacent to the internal jugular vein. Theinsulative material defines a channel within the extravascular space.Energizing the energy delivery, implant causes energy to conduct alongthe channel to the target contents of the sheath.

In some embodiments, the system my include a plurality of electrodesdisposed on the lead, the electrodes including a first array and asecond array, wherein the first and second arrays are positioned suchthat when the first array is positioned in the internal jugular vein todirect stimulation energy transvascularly to a vagus nerve in thecarotid sheath, the second array is positioned to direct stimulationenergy transvascularly towards a carotid artery or carotid sinusnerve/nerve branch within the carotid sheath. In other embodiments, thesame array of electrodes delivers stimulus to each of the targetstructures within the carotid sheath.

The baroreceptors in the aorta are the second best understoodbaroreceptors and are also a powerful localized blood pressure sensingcomponent. The aortic baroreceptors are also responsible for providingsignals to the brain for regulating system/peripheral blood pressure.Some of the embodiments disclosed herein are positioned totransvascularly deliver energy to these baroreceptors and/or associatednerve structures as an alternative means for neurohormonal control.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1A schematically illustrates intravascular positioning of anintravascular neurostimulation system for stimulation of the carotidsinus bulb.

FIG. 1B is a detail view of the area identified by circle 1B-1B in FIG.1A showing the lead anchored in the internal jugular vein.

FIG. 1C illustrates anchoring of the housing in the inferior vena cava.

FIG. 1D is similar to FIG. 1A but shows a bi-lateral arrangement ofstimulation leads.

FIGS. 2A and 2B schematically illustrate the arrangement of the internaljugular vein, carotid artery, and vagus nerve within the carotid sheath.FIG. 2A is a schematic cross-section view of the sheath. FIG. 2B is aside view showing contents of the sheath, with the sheath removed.

FIG. 3A is a schematic representation of an internal jugular vein,carotid bulb and vagus nerve and illustrates a first electrodearrangement for stimulating the contents of the carotid sheath, such asthe carotid artery and vagus nerve.

FIG. 3B schematically illustrates, in cross-section, an internal jugularvein, vagus nerve, and carotid sinus, and schematically shows a secondelectrode arrangement for stimulating the carotid bulb and vagus nerve.

FIG. 3C is similar to FIG. 3B and schematically shows a third electrodearrangement for stimulating the carotid bulb and vagus nerve.

FIG. 4A is a perspective view of a distal portion of an intravascularstimulation lead including a first electrode design which may be used todirect simulation energy towards contents of the carotid sheath.

FIG. 4B is a cross-section view of the carotid sheath showing the leadof FIG. 4A positioned in the internal jugular vein.

FIG. 4C is a perspective view similar to FIG. 4A showing the distalportion of an alternative lead having electrodes suitable for directingsimulation energy towards contents of the carotid sheath.

FIG. 4D is a side elevation view showing the lead of FIG. 5A anchored ina blood vessel.

FIGS. 5A and 5B schematically illustrate positioning of a system withelectrodes in the pulmonary artery for aortic arch baroreceptorstimulation. In FIG. 5B, the pulmonary artery is shown in cross-sectiontaken along the plane indicated by arrows 5B-5B in FIG. 5A.

FIG. 6 schematically illustrates positioning of a system with a leadpositioned to place electrodes for stimulation of aortic archbaroreceptors and the vagus nerve.

FIG. 7A schematically illustrates the region identified by circle 7-7 inFIG. 6 and illustrates a first embodiment of electrode positions for thelead. FIGS. 7B through 7D are similar to FIG. 7A and show alternateembodiments of electrode positions for the lead.

FIG. 8A is a side elevation of a first embodiment of an electrode andanchor structure. The electrode and lead are positioned in a vesselshown in cross-section.

FIG. 8B is a cross-section view taken along the plane designated 8B-8Bin FIG. 8A.

FIG. 9A is a side elevation view showing a second embodiment of anelectrode and anchor structure.

FIG. 9B illustrates the embodiment of FIG. 9A in the collapsed position.

FIG. 9C illustrates an alternative to the electrode and anchor structureof FIG. 9A shown schematically in a mapping position within a bloodvessel.

FIG. 9D is similar to FIG. 9C but shows the electrode and anchor in thefully deployed position.

FIG. 10A is a side perspective view showing a second embodiment of anelectrode and anchor structure.

FIG. 10B schematically shows the FIG. 10A embodiment within a vein inproximity to a carotid sinus bulb. The vein is shown as transparent.

FIG. 11A is a perspective view of a third embodiment of an electrode andanchor structure.

FIG. 11B illustrates sequential deployment of two units of theelectrode/anchor of the FIG. 11A embodiment.

FIG. 12A is a perspective view showing a fourth embodiment of anelectrode and anchor structure, the electrode and anchor are shownpositioned within a vessel which is illustrated as transparent.

FIG. 12B shows the fourth embodiment of FIG. 12A partially positionedwithin a deployment sheath.

FIG. 12C shows the fourth embodiment of FIG. 12A deployed in a bloodvessel which is shown as transparent.

FIG. 13 is a perspective view of an alternative electrode and anchorarrangement.

FIG. 14 schematically illustrates a pair of electrodes positioned inseparate veins on opposite sides of a target neurological structure.

FIG. 15 is a perspective view showing an anchor and lead system, withthe lead fully detached from the anchor. The anchor is schematicallyshown disposed within a portion of a blood vessel, the walls of whichare shown as transparent.

FIG. 16 is a perspective view of the lead of FIG. 15, with the cableremoved from the conductors. The member is shown transparent.

FIG. 17 is a perspective view of the anchor of FIG. 15.

FIG. 18 is a perspective view of the lead and anchor system with theelectrode member disposed in the receiver and with the assembly rotatedto show the exposed surfaces of the electrodes.

FIG. 19 is a perspective view showing a slightly modified embodiment ofan anchor and lead system in which a portion of a blood vessel isschematically shown around the anchor. The anchor is schematically showndisposed within a portion of a blood vessel, the walls of which areshown as transparent.

FIG. 20 is a distal end view of the anchor and lead of FIG. 19 showndisposed within the vessel to illustrate positioning of the electrodebetween the anchor and the vessel wall.

FIG. 21 is a perspective view of an alternate embodiment of a lead andanchor system.

FIG. 22 is a perspective view of the receiver of the embodiment of FIG.21, showing insertion of the electrode member into the receiver.

FIG. 23A schematically illustrates an electric field passing from astimulation electrode in the internal jugular vein.

FIG. 23B illustrates administration of a steering insulative material tosteer the electrode field of an electrode positioned as in FIG. 23A.

FIG. 24 schematically illustrates a method of administering aninsulating material to an interior surface of a vessel wall.

FIG. 25 schematically illustrates a method of ministering an insulatingmethod to an outer surface of a vessel wall.

FIGS. 26A-26D are a sequence of drawings schematically illustratingplacement of a shield in proximity to a vessel.

FIG. 27 illustrates an alternative embodiment utilizing ultrasoundstimulation energy.

FIG. 28 illustrates an insulative shield positioned partiallysurrounding the carotid sheath to block transmission of stimulationenergy to structures external to the carotid sheath.

DETAILED DESCRIPTION

Referring to FIG. 1A, in a first embodiment, system 10 includes ahousing 12 containing the necessary pulse generator and associatedelectronics, circuitry and related components and at least one lead 14carrying some or all of the electrodes 18 needed to deliver electricalenergy to nervous system structures. In the illustrated embodiment, thehousing 12 is positioned in the inferior vena cava (“IVC”), but it mayalternatively be positioned in other vessels including, but not limitedto, the superior vena cava (“SVC”) (see FIG. 6, for example), or theleft or right subclavian vein (“LSV” or “RSV”). An anchor 16 is used toretain the housing within the vasculature. Features suitable for usewith the system, including embodiments of leads, electrodes, housingsand anchors are shown and described in the following patents andapplications, each of which is incorporated herein by reference: U.S.Pat. No. 7,082,336 entitled IMPLANTABLE INTRAVASCULAR DEVICE FORDEFIBRILLATION AND/OR PACING, U.S. 2005-0043765 entitled INTRAVASCULARELECTROPHYSIOLOGICAL SYSTEM AND METHODS, U.S. US 2005-0228471, entitledMETHOD AND APPARATUS FOR RETAINING MEDICAL IMPLANTS WITHIN BODY VESSELS,U.S. Pat. No. 7,363,082, entitled FLEXIBLE HERMETIC ENCLOSURE FORIMPLANTABLE MEDICAL DEVICES, U.S. US 2005-0154437, entitled IMPLANTABLEMEDICAL DEVICE HAVING PRE-IMPLANT EXOSKELETON, and U.S. 2007/0255379,entitled INTRAVASCULAR DEVICE FOR NEUROMODULATION. Each of these priorpatents/applications is incorporated herein by reference.

The lead 14 is intravascularly positioned such that electrodes areoriented to stimulate nervous system structures outside the vesselwithin which the electrodes are placed. In the embodiment shown in FIGS.1A and 1B, the electrodes are placed in the venous system and orientedtowards the carotid bulb CB to allow electrical energy from theelectrodes to be targeted towards the baroreceptors of the carotidartery and/or the carotid sinus nerves or associated nerves or nervebranches. In this embodiment, lead 14 is delivered via the internaljugular vein (IJ) to the location in the neck at the common carotidbifurcation. As best shown in FIG. 1B, an anchor 20 coupled to the lead14 may expand into contact with the walls of the internal jugular veinto maintain the position of the electrodes. From this electrodelocation, neurostimulation therapy can be delivered transvascularly fromelectrodes on the lead or anchor towards the carotid bulb. Stimulationof the barareceptors of the carotid bulb, or the associated carotidsinus nerves and/or nerve branches, activates a baro-response whichcontrols blood pressure for the treatment of hypertension and/or heartfailure.

Referring to FIG. 1D, the FIG. 1A embodiment may be adapted forbi-lateral stimulation as also discussed below in connection with FIG.3. More specifically, electrodes 18 may be anchored in both the left andright internal jugular veins for simulation of the carotid sinus bulbson both the left and right side of the vasculature. The FIG. 1Dembodiment illustrates a tripolar arrangement of electrodes.

In some embodiments, electrodes are intravascularly positioned tostimulate multiple neurological targets. For example, electrodespositioned in the internal jugular for stimulation of carotid sinusnerve targets (e.g. the carotid sinus nerves or associatedbaroreceptors) may also be used to additionally stimulate the vagusnerve.

As illustrated in FIGS. 2A and 2B, the internal jugular IJ, vagus nerveV, and common carotid artery CA (which includes the carotid sinus) arelocated within the carotid sheath S, a fascial compartment within theneck, Sheath S provides relatively fixed geometric relationships betweenthese structures white also giving some degree of insulation from othersurrounding tissue. The embodiments of FIGS. 3A-3C take advantage ofthese geometric relationships in utilizing a single neurostimulationdelivery device for directing electrical energy towards both the vagusnerve and the carotid bulb. According to one such embodiment, a singlelead is delivered to position electrode(s) in the portion of internaljugular vein disposed within the sheath S, i.e. near the site of theright carotid bifurcation as discussed in connection with FIG. 1A-1B.Positioning of the electrode within the carotid sheath may be confirmedusing angiography or carotid ultrasound.

The system operates to stimulate both the vagus nerve and carotid sinusnerve targets using electrodes on the IJ lead. Stimulation of each suchstructure may be achieved using the same set of electrodes 18 a (FIG.3B) utilizing the same electrical stimulation protocol, whilesimultaneously preventing the stimulation of other structures in theneck.

Stimulating the contents of the carotid sheath S can counteractcompensatory mechanisms that drive disease progression in chronic HF.Specifically, such stimulation may be used to reduce sympatheticactivation and enhance sympathetic tone, and to improve hemodynamics(peripheral vascular resistance, afterload, cycle length and strokevolume) to reduce blood pressure and heart rate.

The electrodes 18 a may be positioned to extend both longitudinally(FIG. 3A) and circumferentially (FIG. 3B) along a portion of theinternal jugular, or in any arrangement that will generate stimulationpatterns oriented to capture both the vagus nerve and carotid sinusnerve targets (e.g. the carotid sinus nerves, nerve branches, and/orassociated baroreceptors).

Therapeutic activation of these structures will provide multiplebenefits, including 1) activation of the baro-response to lower bloodpressure, 2) activation of the parasympathetic afferent and efferentpathways to help rebalance the sympathetic/parasympathetic imbalancethat is common in heart failure patients, 3) mild reduction in heartrate (through vagal stimulation) that can reduce total cardiac energyconsumption, reduce diastolic pressures, reduce mean arterial pressures,and possibly reduce afterload.

In a modification to the FIG. 3B embodiment, dedicated electrodes arepositioned for each type of target as shown in FIG. 3C, in whichelectrodes 18 b are positioned to stimulate the vagus nerve whileelectrodes 18 c are positioned to stimulate the carotid sinus.

In one exemplary arrangement shown in FIGS. 4A and 4B, the lead 14 has aspiral-shaped section 15 which may be on the distal section of the lead.Electrodes 18 a are positioned on the spiral 15 such that electrodesline up in multiple circumferentially spaced longitudinal arrays, suchas arrays A1, A2 and A2 as shown. As can be seen in the cross-sectionview of FIG. 4B, when the lead is implanted a first one of the arrays A1is positioned to direct stimulation energy towards the carotid artery orassociated carotid sinus nerve targets, and a second one of the arraysA2 is positioned to direct stimulation energy towards the vagus nerve.Determination of which of the arrays is located for the most optimalstimulation of which structure may be determined during implantation bymeasuring blood pressure and heart rate feedback, or related parameters.This allows the user to program the stimulation device to energize theelectrodes in array A1 in accordance with a stimulation algorithm bestsuited for stimulation of the carotid artery or carotid sinus nervetargets, and to energize the electrodes in array A2 in accordance with astimulation algorithm best suited for vagal nerve stimulation.

In an alternative embodiment, the arrays of electrodes may be positionedon an expandable stent-like anchor of the type described below inconnection with FIG. 9A, for example. See also FIGS. 3A-3C. The anchormight take the form of a self-expandable mesh formed of a polymericmaterial or other insulated material. With this form of anchor, theanchor can be provided with insulation around a majority of itscircumference, allowing stimulation energy to be directed only towardsthe target structures, thereby minimizing collateral stimulation. Itshould be noted that white “stent-like” anchors resemble stents thesense that they are expandable so as to radially engage a vascular wall,the anchors need not have the hoop strength possessed by conventionalstents as needed by such sterns to maintain patency of the diseasedvessels within which they are conventionally implanted.

In another alternative shown in FIGS. 4C and 4D, the lead 14 includes afirst, longitudinal, section 17 including a first electrode array havingelectrodes 18 a positioned to direct energy towards the carotid arteryand/or carotid sinus nerve or associated nerve structures. Thelongitudinal section 17 may be pre-shaped to include a laterallyextending curve having a spring force that will bias the associatedelectrodes 18 a on the longitudinal section 17 in apposition with thevessel wall. A second section 19 has a second electrode array havingelectrodes 18 b positioned to direct energy towards the vagus nerve. Thesecond section 19 may be partially circumferential as shown, no that theelectrodes 18 b are spaced generally circumferentially to optimizecapture of the vagus nerve. One or more anchors 16 may be used tosupport the lead as shown.

Further alternatives to the FIG. 3A-3C embodiment include delivering alead to both the right and left side of the neck for bilateralstimulation of the carotid bulbs white only stimulating the right sidevagus nerve, 2) delivering a lead to both the right and left side of theneck for bilateral stimulation of the carotid bulbs and bilateralstimulation of the vagus nerve (see e.g. FIG. 1D), 3) utilizing any ofthe previously described lead configurations but utilizing separateenergy delivery protocols for stimulating the carotid baro-response andvagal nerve. Implementations of this tatter concept might include (a)interleaving/multiplexing (time sequencing where an “a” therapy is onfor a pre-determined or adaptively determined duration followed by a “b”therapy that is on for a predetermined or adaptively determined time ina repeating “a”/“b” sequence) the delivery of two separate electricalstimulation protocols utilizing the same stimulation electrodes or (b)having a multiplicity of electrodes on the lead such that one set ofelectrodes can be utilized to uniquely stimulate the carotidbaro-response and a second set of electrodes can be utilized to uniquelystimulate the vagus nerve (e.g. as in the FIG. 4A-4C embodiments), thesetherapies would be independent of each other so could be deliveredsimultaneously but could also be sequenced as described in (a).

In another embodiment, electrodes anchored in the pulmonary artery maybe used to simulate neurological targets associated with baroreceptorsof the aortic arch. Such targets can include the baroreceptorsthemselves or the associated nerves. As discussed in the Backgroundsection, the aortic baroreceptors are a powerful localized bloodpressure sensing component and are also responsible for providingsignals to the brain for regulating systemic/peripheral blood pressure.The present embodiment takes advantage of the positional relationshipbetween the aortic arch and the pulmonary artery to position electrodesfor stimulation of the aortic baroreceptors. In the human anatomy, theaortic arch crosses the pulmonary artery above the pulmonary arterybifurcation. At this point the pulmonary artery and the aortic arteryare in intimate contact. The aortic baroreceptors are co-located at thispoint. All of these structures are co-located within the thoracic cavityand remain in a relatively fixed geometric relationship. The followingembodiment utilizes a single neurostimulation delivery device forstimulating the aortic arch and activating a baro response for bloodpressure control in the treatment of hypertension or congestive heartfailure.

In a preferred configuration for implementing this embodiment, a singleintravascular lead is delivered to the site of the pulmonaryartery/aortic arch intersection point. The lead is anchored in thepulmonary artery at this location no as to position the electrodes foroptimal stimulation of the aortic arch baroreceptors, whilesimultaneously preventing the stimulation of other structures in thechest cavity. FIGS. 5A and 5B illustrate that by positioning theelectrodes 18 c at or near the portion of the pulmonary artery PAcrossing over the aortic arch 8, the electrical field can be directedtowards the aortic arch. Access to the pulmonary artery can be gained byextending the electrode leads through the IVC or SVC to the rightatrium, then into the right ventricle and out of the heart into thepulmonary artery. See FIG. 5A. The device would be capable of all thestimulation protocols, isolation/insulation, utilization of sensors,external communication and programming, energy/power sources, implanttools and techniques as used for the jugular based system, includingthose disclosed herein and in Applicant's prior Application PublicationNo. U.S. 2007/0255379.

Alternatives to the FIG. 5A embodiment include other venous routes fortransvenous stimulation of the aortic arch baroreceptors. For example anintravascular lead could be positioned in the left innominate vein.Other baroreceptors besides those clustered in the aortic arch may bestimulated with this device. For example, electrodes could be positionedwithin the pulmonary artery (main, left, right, or any combination ofthese) in order to stimulate pulmonary artery baroreceptors. This may beperformed in isolation or in combination with stimulation directedtoward the baroreceptors of the aortic arch. This is one example of manypossible target combinations that could be utilized in transvascularbaroreceptor stimulation from within the great vessels

The embodiment of FIGS. 5A-5B may be further modified to include vagusnerve stimulation in additional to stimulation of barareceptors of theaortic arch (or associated nerves). Examples of electrode placementaccording to this embodiment are illustrated in FIGS. 7A through 7C,each of which represents the region of the heart and neighboringvasculature defined by the region marked by circle 7-7 in FIG. 6. Inthese figures, anchors for the portion of the lead carrying theelectrodes are not shown for clarity.

Referring to FIG. 6, in the human anatomy the aortic arch crosses thepulmonary artery above the pulmonary artery bifurcation; at this pointthe pulmonary artery and the aortic artery are in intimate contact. Theaortic baroreceptors are also at this location. A branch of the vagusnerve follows the crease at the base of the heart (more or less thedivision between the upper and tower chambers of the heart). Efferentfibers innervate the right atria and are involved in the control ofheart rate. Afferent fibers continue to the location of the aortic archbaroreceptors and conduct signals back to the brain for control ofsystemic blood pressure. The current embodiment utilizes a singleneurostimulation delivery device for activating both the vagus nerve andthe baroreceptors of the aortic arch.

Referring to FIG. 7A, in a first embodiment, a single intravascular lead14 is delivered to the site of the pulmonary artery/aortic archintersection point. The lead 14 is anchored in the pulmonary artery atthis location in such a way as to position the electrodes 18 d foroptimal stimulation of the aortic arch baroreceptors, and to positionthe electrodes 18 d in the early pulmonary artery for stimulation of thevagus nerve. This arrangement allows simulation of the vagus nerve andaortic arch baroreceptors from the same lead, potentially utilizing thesame electrical stimulation protocol, while simultaneously preventingthe stimulation of other structures in the chest cavity. In analternative to this arrangement, separate leads may be used to positionthe electrodes 18 d and the electrodes 18 e. For example, one methodmight include delivering one lead to the pulmonary artery at theintersection with the aortic arch, such that stimulation electrodes 18 dare optimally positioned and anchored to stimulate the aortic archbaroreceptors, and delivering a second lead having electrodes 18 e tothe outflow track of the pulmonary, such that electrodes 18 e arepositioned and anchored to optimally stimulate the vagus nerve.

In an alternate embodiment shown in FIG. 7B, lead 14 is delivered to thepulmonary artery at the intersection with the aortic arch. Stimulationelectrodes 18 d are optimally positioned and anchored to stimulate theaortic arch baroreceptors. This embodiment differs from the FIG. 7Aembodiment in that here electrodes 18 e for stimulating the vagus nerveare positioned closer to the aortic arch. This embodiment might be evenfurther modified as shown in FIG. 7C, so that a single array ofelectrodes 18 d is used for both aortic arch baroreceptor stimulationand vagus nerve stimulation.

In the FIG. 7D embodiment, lead 14 is delivered to the pulmonary arteryat the intersection with the aortic arch, to optimally position andanchor the stimulation electrodes 18 e to stimulate the aortic archbaroreceptors. A second lead 14 a is delivered to either the rightatrium (shown) or to the right ventricle. Second lead 14 a includes aseparate set of stimulation electrodes 18 e positioned and anchored tooptimally stimulate the vagus nerve.

In any of the exemplary electrode/lead configurations, stimulation maybe performed using the same energy delivery protocols for both aorticarch baroreceptor stimulation and vagus nerve stimulation.Alternatively, any of the lead/electrode configurations might utilizeseparate energy delivery protocols for stimulating the aortic archbaroreceptors and vagal nerve. Several ways in which this could beaccomplished include: (a) interleaving/multiplexing (time sequencingwhere “A” therapy is on for a pre-determined or adaptively determinedduration followed by a “B” therapy that is on for a predetermined oradaptively determined time in a repeating “A”/“B” sequence) the deliveryof two separate electrical stimulation protocols utilizing the samestimulation electrodes or (b) having a multiplicity of electrodes on thelead such that one set of electrodes can be utilized to uniquelystimulate the carotid baro-response and a second set of electrodes canbe utilized to uniquely stimulate the vagus nerve, these therapies wouldbe independent of each other so could be delivered simultaneously butcould also be sequenced as described in (a).

The therapy performed using the configurations of FIGS. 7A-7D canprovide multiple benefits, including (1) activation of the baro-responseto lower blood pressure, (2) activation of the parasympathetic afferentand efferent pathways to help rebalance the sympathetic/parasympatheticimbalance that is common in heart failure patients, (3) mild reductionin heart rate that can reduce total cardiac energy consumption, reducediastolic pressures, reduce mean arterial pressures, and possibly reduceafterload.

The electrodes may be configured in a uni-polar, bipolar, tri-polararrangement, or they may be arranged in an array for selectiveactivation. Various configurations for anchoring or supporting theelectrodes and lead may be implemented.

Referring to FIG. 8A, the anchor may take the form of a stent-typedevice 20 that is expandable into contact with the walls of the vesselto maintain its position with the vessel. Electrodes 22 are attached to,or integral with, the stent. The stent may be balloon expandable orself-expanding. Suitable stent materials include polymeric materialsand/or metals. In the illustrated design, stent 20 is formed of discretemetallic segments. A distal one of the segments 22 a functions as anegative electrode and a proximal one of the segments 22 b functions asa positive electrode. Each of the segments 22 a, 22 b has acorresponding conductor 24 a, 24 b that extends through the lead 14 topulse generator housing 12 (FIG. 1A). The segments 22 a, 22 b may becompletely separate from one another as shown, other embodiments, thesegments may be coupled to or are integral with one another, in whichcase remaining portions of the stent (e.g. between the segments) areinsulated or formed of non-conductive material. Additionally, as shownin FIG. 8B, a portion of the circumference of each electrode segment 22a, 22 b is masked using an insulative polymeric coating such that thesegment is conductive around less than its 360 degree circumference,allowing the stent to preferentially direct the electric field towardsthe target area from the unmasked region 23.

In another embodiment, a polymeric stent or non-conductive braid may beprovided with electrodes mounted to it such that the electrodes arepositioned in contact with the vessel wall when the stent or braid isexpanded. For example, as shown in FIG. 9A, four distal electrodes 26a-d are positioned at 90 intervals around the circumference of a distalportion of braid 28, and four proximal electrodes 26 e-h are similarlypositioned. Conductor wires 30 a-h (not all of which are visible) extendfrom corresponding ones of the electrodes 26 a-h through the lead 14.Any number of techniques may be used for mounting the electrodes to thestent. In the embodiment shown in FIG. 9A, an adhesive is used to mountthe electrodes to the outer circumferences of silicone rings 32 a, 32 bpositioned within or surrounding the braid 28. The braid may beself-expandable, or it might employ an active expansion mechanism, suchas an outer tube 34 mounted to the proximal end of the braid and aninner tube 36 mounted to the distal end of the tube such that the braidmay be expanded by withdrawing the inner tube as shown in FIG. 9B. Theinner tube 36 may include a guidewire lumen which allows the braid to betracked over a guidewire for implantation.

In a modification to the FIG. 9A embodiment, electrodes external to thebraid are positioned on wires that are woven through the braid. In yetanother alternative, a stent or braid configuration may alternatively beexpanded to “sandwich” separately introduced electrodes (e.g. electrodesmounted on a conductor positioned parallel to the braid) between thestent/braid and the vessel wall.

FIGS. 9C and 9D illustrate an embodiment in which the anchor (with theelectrodes coupled thereto as described) is configured to allow partialdeployment for mapping purposes before the anchor is fully deployed atits final location. The anchor 37 is initially disposed within anintroducer sheath 39. The distal end of the anchor 37 is containedwithin a tubular end cap 41. An inner tube or mandrel 36 extends throughthe sheath and the anchor and is attached to the tubular end cap 41. Theintroducer sheath 39 is advanced to a target position within the vesseland the anchor 37 is partially advanced from the introducer sheath 39.At this stage, the anchor 37 may be in a position similar to that shownin FIG. 9B with respect to the prior embodiment. The mandrel 36 is thenmoved proximally to expand the anchor into the partially deployedposition shown in FIG. 9C. Mapping tests are performed by deliveringstimulation energy from the electrodes on the anchor and measuring theresponse (e.g. blood pressure, heart rate, and/or related parameters).The mandrel is advanced distally to partially collapse the anchor andthe anchor is moved to a second location. The anchor is re-opened to thepartially deployed position as described above and additional mappingprocedures are performed. The process is repeated until the anchorelectrode position is optimized. The anchor is fully deployed bydetaching the cap 41 from the distal end of the anchor (e.g. byrotation, electrolytic detachment or other means), thereby allowing thedistal end of the anchor to fully expand. The mandrel 36 and introducer39 are withdrawn, leaving the electrode anchor 37 and lead disposed inthe vessel.

Alternative embodiments use structures other than stents or braids tosupport the electrodes against the vessel walls. For example, FIG. 10Aillustrates an embodiment in which the electrodes 38 are supported bytines 40 that expand outwardly to position the electrodes in contactwith the vessel wall. The tine and electrode shown in dashed linesillustrates the spring bias exhibited by the tines when they are notrestrained by a sheath or vessel wall. Separate conductors 42 for eachof the electrodes run through the lead 14. During implantation thephysician will select the combination of electrodes that will cause theelectric field to reach to the target neurological structures as shownin FIG. 10B.

In another alternative embodiment shown in FIG. 11A, an electrodecarrying anchor 45 includes a collection of struts 46 coupled to anouter tube 48 at their proximal ends and to an inner tube 50 at theirdistal ends 50. The inner tube 50 extends through the outer tube 48 suchthat relative movement away from one another places the struts in anelongated position for passage through the vasculature. Relativemovement of the tubes 48, 50 towards one another causes the struts toexpand outwardly into contact with a vessel wall when a delivery sheathrestraining the struts is withdrawn or removed. Each strut may itselffunction as an electrode insulated from the other struts, and the strutswhich are to be energized may be determined in a mapping procedure. Inother embodiments several of the struts of an anchor may be insulated,with the remaining struts conductive and operable as electrodes.Alternatively, sections of conductive struts may be masked off to leaveone or more conductive regions. In other embodiment, electrodes may bemounted to the struts such that expansion of the struts positions theelectrodes into contact with the vessel wall.

FIG. 11B illustrates that a pair of the FIG. 11A devices 45 may bedeployed in sequence from a sheath 47 within a blood vessel. In thedrawing, the second of the two devices 45 has not yet been deployed, butits intended position following deployment is shown in dashed lines.These electrode anchor devices are coupled to the pulse generator suchthat one of the devices 45 functions as the negative electrode and theother functions as a positive electrode.

FIGS. 12A through 12C illustrate an alternative design of an electrodeand anchoring device designed to push the electrodes into contact withthe vessel wall (shown in dashed lines in the drawings). This embodimentis advantageous is that it is re-sheathable into a catheter within thebody, allowing repositioning of the electrodes if necessary to gainbetter access to a stimulation target. Referring to FIG. 12A, lead 14includes a plurality of band electrodes 60, each having an insulatedconductor wire 62 extending through the lead. A plurality of nitinolspring members 64 extend from the lead 14 and include a free end 68formed to have an atraumatic curvature. As best shown in FIG. 12B, whenthe lead 14 is positioned within a deployment sheath 66, spring members64 are compressed such the free ends 68 are moved towards the lead 14.When the lead 14 is advanced from the sheath 66, the free ends springoutwardly into contact with the vessel wall, thereby pressing theelectrodes 60 into contact with an opposite side of the vessel wall. Thespaced apart positioning of the spring members allows electrode contactwith the vessel wall to occur even when the electrodes are situatedwithin a bend in the vessel as shown in FIG. 12C.

In another embodiment of an electrode anchor device shown in FIG. 14, anarray of electrodes 60 a is disposed on an elongate member 63. Themember 63 is formed of flexible substrate (e.g. silicone). The member ispreferably shaped to have a convex face 67 positionable in contact withthe vessel wall. The substrate encapsulates the distal portions of theconductors 62 a and partially encapsulates the electrodes 60 a, leavingthe electrodes exposed on the convex face 67 for contact with theinterior of the vessel wall. The electrodes include pass through lumens65 which allow the conductors 62 a to be routed through electrodesrather than routed around them.

In an alternate embodiment, the electrodes may instead be formed onto orattached to one face of the member 63.

The anchor 64 a is comprised of one or more resilient elements 67extending laterally from the member 63. The resilient elements arepreferably curved so as to extend partly or fully circumferentiallyalong the vessel wall. In the illustrated embodiment, nitinol wires areshaped to include a plurality of v-shaped hoop sections defining theresilient elements 67, with each member curving outwardly from itsorigination at the substrate and then curving inwardly to give themember a partially circumferential shape. Two such wires are shown, eachdefining three opposed elements 67. In other embodiments, each elementmay be discrete from the other elements. In still other embodiments, theelements may be more fully circumferential (e.g. hoops of the type shownin FIG. 18).

As illustrated in FIG. 14, in an alternative embodiment, separateelectrodes are placed in separate veins V1, V2 positioned on oppositesides of the nerve structure or baroreceptor T that is the target of thestimulation energy. In this embodiment, electrode structures such asthose described above may be used. Alternatively, the electrodes 70 a,70 b may instead be elongate sections of conductive wire or ribbonhaving a small cross-section that allows access to smaller vessels. Asillustrated by the field lines in FIG. 13, activation of electrodes inthis arrangement allows the electric field to extend from one vessel tothe other. The positioning of the electrodes is fine-tuned as indicatedby arrows by adjusting the longitudinal position of each electrode inits corresponding vessel, such that the generated field passes throughthe target neurological structure T.

FIGS. 15 through 22 illustrate an alternative intravascular anchorhaving a lead that may be detached from the anchor in situ, allowingexplantation of the lead while leaving the anchor in place within theblood vessel. When a lead is chronically implanted within a bloodvessel, tissue or other material may grow, form or accumulate on partsof the device (e.g., through cellular encapsulation, in-growth,endothelialization, thrombosis, etc.). When it is time to remove a leadfrom the patient, the tissue growth may complicate the extractionprocess, particularly with respect to the anchor which is in contactwith the vessel wall. In some instances, it may be desirable to separatethe lead from the anchor and to extract the leads while leaving theanchors in the blood vessel, so as to minimize the risk of damage to thevessel wall. The FIG. 15 through 22 embodiments show a lead and anchorsystem that permits extraction of a lead while leaving the associatedanchor behind. The following discussion also describes a method fordetaching a lead from an anchor, and for optionally replacing theexplanted lead with a new lead.

These embodiments are shown and described with respect to electricalleads for use in delivering electrical stimulation to nervous systemtargets as discussed above, or to tissue of the heart, using electrodes.However it is to be understood that these concepts may be used for leadsthat take the form of fluid conduits for delivery of therapeutic ordiagnostic agents. In still other embodiments, the leads may be used forcommunication of signals representing parameters sensed within thevasculature using sensors on the leads.

Referring to FIG. 15 system 100 generally includes an anchor 114, a lead116, and an electrode array 118 on the lead 116. Array 118 includes aplurality of electrodes 120 a-c. In FIG. 15, a blood vessel W isschematically illustrated surrounding the anchor 114.

Lead 116 includes an elongate cable 122 which houses conductors 124 a-cthat are electrically coupled to the electrodes 120 a-c. A member 126formed of flexible substrate (e.g. silicone) encapsulates the distalportions of the conductors 124 a-c and partially encapsulates theelectrodes 120 a-c, leaving exposed faces 132 on one side of the member126. The electrodes are provided with pass through lumens 134 whichallow the conductors 124 a, 124 b to be routed through electrodes ratherthan routed around them.

In an alternate embodiment, the electrodes may instead be formed onto orattached to one face of the member 126.

Anchor 114 is preferably an expandable device radially compressible intoa collapsed position for loading into a deployment sleeve forintravascular introduction into a target blood vessel. The device isradially expandable upon release from the deployment sleeve, so that itcan expand into contact with the wall of the blood vessel W a targetsite. The anchor has structural features that allow it to radiallyengage the vessel wall using forces sufficient to maintain thepositioning of the anchor at the target site, but not necessarilysufficient to perform the functions of a stent. The anchor might be atubular band, sleeve, mesh, braid, laser cut tube, or other frameworkformed of one or more shape memory (e.g. nickel titanium alloy,thermally activated shape-memory material, or shape memory polymer)elements or stainless steel, Elgiloy, or MP35N elements.

The anchor 114 includes a receiver 136 positioned to receive the member126 so that the electrodes supported by the member are retained at adesired position within a blood vessel. In the embodiment shown in FIGS.15-18, the anchor 114 includes a plurality of hoops 134 in which aportion of the hoop 134 curves radially inwardly and then outwardly todefine a receiver section 137. The hoops 134 are positioned in thevessel W such that the receiver sections 137 are longitudinally alignedas shown in FIG. 15, thus forming receiver 136 bounded by the receiversections 137 of the hoops on the radially inward side and by thevascular wall W on the radially outward side. The receiver 136 isdimensioned to slidingly receive the member 126 and to support it withinthe vessel W as shown in FIG. 15, so that the exposed sections 132 (FIG.18) of the electrodes are biased in contact with the vessel walls.

The hoops 134 may be individual hoops positionable in a spaced apartarrangement within the blood vessel. In the FIG. 15-18 embodiment, thehoops 134 are arranged in a proximal grouping and a distal grouping,wherein the proximal and distal groupings are separated by an elongatespace S. The space S may equal or exceed the longitudinal separationdistance between the distalmost portion of the most distal electrode inthe array and the proximalmost portion of the most proximal electrode.Although the illustrated proximal and distal groupings include two hoopsin the distal grouping and three hoops in the proximal grouping, othernumbers of hoops may be used. In another embodiment, either or both ofthe proximal and distal groupings may include only a single hoop.

In other embodiments all of the hoops, or each of the proximal anddistal groupings of the hoops, may be coupled together by struts, asleeve, or other elements made from polymeric material, ePTFE, or othersuitable materials. In the embodiment shown in FIGS. 19 and 20,longitudinal struts 138 extend between the hoops 134. These struts 138are disposed in the receiver sections 136, and bow slightly outwardly attheir midsections, helping to bias the member 126 and thus the electrodesections 132 into contact with the wall of the surrounding vessel V.Tabs 140 are optionally positioned on the proximal end of the struts 138and can be used for docking a lead removal device as will be describedbelow.

To deploy the system 100, the anchor 114 is radially compressed into acollapsed position and loaded into a deployment sleeve. Using knowntechniques, the deployment sleeve is percutaneously introduced into thevasculature and advanced to the target blood vessel where the electrodesare to be anchored. The anchor 114 is released from the deploymentsleeve and allowed to expand within the vessel. Where the anchor 114 iscomprised of separate hoops, the anchor may be released in sequentialsteps in which a distalmost one of the hoops 134 is pushed from thedeployment sleeve, and the deployment sleeve is then withdrawn slightly.The next one of the hoops 134 is pushed from the deployment sleeve intothe vessel, and the process is repeated for each of the hoops. Theamount by which the deployment sleeve is withdrawn after each hoop isreleased determines the spacing between the hoops.

Once the anchor 114 is deployed, the member 126 is advanced into thereceiver 136 as indicated by arrow A1 in FIG. 15, and it is advanceddistally to position the member 126 within the receiver as shown in FIG.19. The member 126 is retained within the vessel between the anchor 114and the vessel wall as shown in FIG. 20. When the member 126 is in theretained position, the exposed faces 132 of the electrodes (preferablyace outwardly as shown in FIG. 18, such that they are in contact withthe surrounding vessel wall.

At times it may be necessary to remove the lead from the anchor. Forexample, lead removal might be desirable if the electronic deviceenergizing the electrode is no longer in use, or because the lead is notfunctioning properly and should be replaced. FIGS. 21-25 illustrate amethod for removing the lead 116 from the anchor 114. When lead removalis needed, a lead removal/exchange catheter is advanced over theproximal end of the lead cable 122. This step may be achieved bydetaching a proximal portion of the lead from the device body 12 (FIG.1), and then passing the removal catheter over the free end of the lead.When the distal end of the removal catheter has reached the anchor 114,it may be coupled to a proximal portion of the anchor 114, such as thetabs 140 or another feature, so as to dock the removal catheter to theanchor.

A guidewire is passed through the retrieval catheter and into thereceiver 136 within which the distal portion of the lead (at member 126)is disposed. The retrieval catheter is held in place while the lead 116is withdrawn into it using tension applied to the proximal end of thelead 116.

If a new lead is to be introduced into the receiver 136, the old leadmay be fully withdrawn from the retrieval catheter and out of the body,leaving the catheter in place for use in providing a passage for the newlead into the vessel. Alternatively, the retrieval catheter with the oldlead inside it may be withdrawn from the body, leaving the guidewire inplace. A second catheter is advanced over the guidewire and (optionally)docked to the anchor as described above. The replacement lead isadvanced distally through the catheter and inserted into the receiver136.

In an alternate arrangement, the member 126 of the lead 116 is providedwith an opening that may be threaded over the guidewire, allowing thelead 116 to be tracked over the wire into the receiver 136. The openingmay be a bore formed in the material of the member, or it may be a loopof suture or other material that is coupled to the member.

FIG. 21 shows an alternative embodiment using a modified form ofreceiver on an anchor 114 a. In this embodiment, the receiver 146comprises an elongate member having a longitudinally extending channel148. The receiver is proportioned to receive the flexible member 126 ofthe lead 116 within the channel 148 such that the exposed surfaces 132of the electrodes face outwardly towards (and ideally in contact with)the vessel wall.

The elongate member is mounted to or formed on the anchor, such as onthe inner or outer wall of the anchor. It is preferably inwardlyrecessed from the radially outermost boundary of the anchor (as with thereceiver 136 of the first embodiment) so that the exposed surfaces 132will be generally flush with or inset from the exterior of the anchorwhen the anchor and lead are implanted. However in other embodiments,the configuration may be such that the exposed surface are positionedradially outwardly of the exterior surface of the anchor. The anchor 114a may take any of the forms disclosed above. The member 126 isinsertable into and removable from the receiver 146 as described above,allowing explantation and or replacement of the lead white the anchorremains in the vessel.

In the disclosed embodiments, optimal stimulation results are achievedwhen the electrodes are positioned to direct the stimulation energytowards the neurological target while minimizing conduction of theenergy to unintended targets. As shown in FIG. 23A, the electric fieldpatterns from a stimulation electrode 18 within the internal jugular canextend through a broad area, creating unwanted collateral stimulation ofnerves other than the target structures T, possibly causing unintendedphysiological responses. Referring to FIG. 23B, syringes 76 may bepassed through the skin and used to inject insulative steering materials78 into the space between the jugular vein and the carotid artery,creating a shield protecting areas away from the target area T fromcollateral stimulation. In one example, fatty material (which may be fatextracted from the patient's own body) is used to create the shield.Alternate examples of injectible materials include silicone or otherbiocompatible insulating materials, including thixotropic materials(which have low viscosity when subjected to stresses during injectionusing a syringe, but which increase in viscosity once injected) andpolymers that may be cured using light, energy, or other substancesfollowing injection.

The injected material forms or defines a channel 80 between the jugularand the carotid artery. The channel provides a conductive path forcurrent passing from the electrode to the region of the carotid artery.In other embodiments, rather than being used to form a channel, theinjected materials may be injected onto specifically identified musclesor nerves for which collateral stimulation is undesired. In theseembodiments, the injected polymers or other materials form an insulativeblanket or cover over the identified muscles or nerves to prevent theelectrical stimulation from causing adverse side effects resulting fromstimulation of those muscles or nerves.

Fluid substances or materials may alternatively be delivered onto theinterior or exterior surface of a vessel containing the stimulationelectrodes (e.g. the internal jugular vein) as a way of shieldingportions of the vein circumference so that the simulation energy willonly conduct through the unshielded portions of the vessel. Suchmaterials may also or alternatively be delivered onto the interior orexterior surface of a vessel other than the vessel containing theelectrodes (e.g. a vessel targeted by or in the path of the stimulationenergy, such as the carotid artery), in order to limit conduction ofstimulation energy beyond a desired region of that vessel.

The delivered materials or substances may be insulative polymers of thetype described above, or they may be materials which cause modificationof the vessel tissue (e.g. necrosis, ablation) to reduce theconductivity of the vessel tissue in areas through which conduction ofstimulation energy is undesirable. Methods for delivering the materialsinclude introducing a catheter 302 to the target site as shown in FIG.24. The catheter includes distally positioned pores or other deliveryports 306 around a portion of its circumference. The ports arepreferably on a balloon 304 carried by the catheter but they may be onthe catheter itself. The balloon may be shaped such that the ports arelocated a reduced diameter portion of the balloon, so that the exteriorof the balloon in this location will form a reservoir R between thevascular wall W and the balloon wall as shown in FIG. 24, allowing theinjected material to accumulate in that portion of the vessel duringcuring. Radiopaque markers on the catheter and/or balloon may bepositioned to identify the region of the balloon having the ports. Theballoon is positioned at the delivery site and longitudinally andaxially positioned such that the delivery ports are positioned to directthe substance onto the tissue through which electrical conduction isdesired to be blocked. Light or other energy may be delivered throughthe balloon wall onto the material using an energy source 308 positionedwithin the balloon.

In an alternative method, a polymeric material 78 may be delivered ontothe exterior surface of the vessel W using a needle 76 passed throughthe skin as shown in FIG. 25.

In another exemplary shielding technique, a minimally invasive surgicaltechnique is used to implant an insulative shield surrounding theexterior wall of vessel W. The shield may be formed of a thin flexibleinsulative sheet or member positioned on or around the vessel exterior.In one exemplary method for implanting the member shown in FIGS.26A-26D, a small incision or is formed to give access to the targetvessel (e.g. the carotid artery or internal jugular). An access cannula310 may be positioned within the incision to provide access for otherinstruments. A dissecting balloon 312 is introduced through the accesscannula 310 and used to dissect the region surrounding the targetvessel, creating a tunneled space T. The shield 314 is delivered to thetunneled space T via the access cannula 310. Other instruments passedthrough the access cannula 310 (or separate incisions) may be used tosecure the shield 314 using sutures, tissue adhesives, or other means.The shield 314 may be wrapped or curled fully or partially around thevessel circumference, depending upon the area of vessel tissue that isto be shielded. The shield may be wrapped around the carotid artery orthe internal jugular vein.

In alternate procedures, such a shield may be implanted through a smallincision formed in the skin of the neck and wrapped around fully orpartially around the carotid sheath.

For example, a shield 316 may be positioned partially or fullysurrounding the carotid sheath S as shown in FIG. 28 to block conductionof the stimulation energy beyond the sheath. The shield may be a sheetof flexible insulative material as shown, or it may be a substanceapplied to the outer surface of the sheath or an insulative substanceinjected into the surrounding space. In the FIG. 28 example, a sutureloop or other connector 320 may passed through the bifurcation betweenthe sheath and the fascial tube containing the external carotid artery.The shield can be made of a material that is highly elastic so as toprevent constriction of the contents of the carotid sheath.

Other exemplary shielding methods may include chemical or electricalablation of nerve or muscle tissue to minimize conduction of electricalstimulation energy to those tissues no as to minimize collateralstimulation effects such as muscle twitches.

Although the majority of this description has been devoted to the use ofelectrical energy to stimulate the nervous system targets, FIG. 27 showsthat the system 10 of FIG. 1A may be modified to replace the electrodeswith an ultrasonic transducer or transducer array 70 that will produceacoustic or ultrasonic energy, shock waves, vibration, etc. Thetransducers are positioned at a location within the internal jugularthat allows a focused pressure wave to impinge upon the carotid sinus,causing vibrations to simulate stretching of the vessel walls. Detectionof a simulated wall stretch by the baroreceptors will promptvasodilation, heart reduction and thus blood pressure reduction.Alternatively, direct ultrasound stimulation of nervous system targetsmay be utilized. In either case, certain ones of the transducers may beemployed to cancel the effect of energy from others of the transducersas a means for minimizing the amount of energy propagating tonon-targets. In other embodiments, transducers may be arranged toproduce intersecting waves of intensity and phase that will combine toproduce a therapeutic dose.

White various embodiments of the present invention have been describedabove, it should be understood that they have been presented by way ofexample, and not limitation. It will be apparent to persons skilled inthe relevant art that various changes in form and detail may be madetherein without departing from the spirit and scope of the invention.This is especially true in light of technology and terms within therelevant art(s) that may be later developed. Thus, the present inventionshould not be limited by any of the above-described exemplaryembodiments, but should be defined only in accordance with the followingclaims and their equivalents. The terms “first,” “second” and the like,where used herein, do not denote any order, quantity, or importance. Inreferences to “first blood vessel”, “second blood vessel” etc., thefirst and second blood vessels may be different blood vessels or theymay be the same blood vessel unless otherwise specified.

Any and all patents, patent applications and printed publicationsreferred to above, including patent applications identified for purposesof priority, are incorporated herein by reference.

1. A method for intravascularly stimulating contents of the carotidsheath, comprising: intravascularly advancing an energy delivery elementinto an internal jugular vein; retaining the energy delivery element ina portion of the internal jugular vein contained within a carotidsheath; and energizing the energy delivery implant to transvenouslydirect energy to target contents of the carotid sheath external to theinternal jugular vein.
 2. The method of claim 1, wherein energy isdirected to a carotid artery within the carotid sinus sheath.
 3. Themethod of claim 1 wherein energy is directed to a carotid sinus nerve ornerve branch within the carotid sinus sheath.
 4. The method of claim 1wherein energy is directed to a vagus nerve or nerve branch within thecarotid sinus sheath.
 5. The method of claim 1 wherein energy isdirected to nerve branches emanating from carotid artery baroreceptors.6. The method of claim 1, further including intravascularly advancing asecond energy delivery element into a second internal jugular vein;retaining the second energy delivery element in a portion of the secondinternal jugular vein contained within a second carotid sheath; andenergizing the second energy delivery implant to direct energy tocontents of the second carotid sheath external to the second internaljugular vein retaining the neurostimulation implant within the firstblood vessel; and positioning at least one electrode within the patient,the electrode in communication with the neurostimulation implant, andstimulating the nervous system target using the electrode.
 7. The methodof claim 1 wherein the energy is electrical energy.
 8. The method ofclaim 1 wherein the energy is ultrasound energy.
 9. The method of claim1, further including positioning a shield at least partially surroundingthe carotid sinus sheath, wherein the shield blocks conduction of energybeyond the sheath during energization of the energy delivery implant.10. The method of claim 1, further including delivering an insulativematerial into extravascular space adjacent to the internal jugular vein,the insulative material defining a channel within the extravascularspace, and wherein energizing the energy delivery implant causes energyto conduct along the channel to the target contents.
 11. The method ofclaim 10 wherein the material includes a fat.
 12. The method of claim 10wherein the material includes silicone.
 13. An intravascular system forstimulation of contents of a carotid sheath, the system comprising: apulse generator positionable within a blood vessel; a lead coupled tothe pulse generator; an anchor adapted to anchor the lead in a portionof an internal jugular vein disposed in a carotid sinus sheath; aplurality of electrodes disposed on the lead, the electrodes including afirst array and a second array, wherein the first and second arrays arepositioned such that when the first array is positioned in the internaljugular vein to direct stimulation energy transvascularly to a vagusnerve in the carotid sheath, the second array is positioned to directstimulation energy transvascularly towards a carotid artery or carotidsinus nerve within the carotid sheath.
 14. The system of claim 13,wherein the first and second arrays are independently energizable by thepulse generator.
 15. The system of claim 13 wherein the first and secondarrays are simultaneously energizable by the pulse generator.
 16. Thesystem of claim 13, further including a shield positionable at leastpartially surrounding the carotid sheath, the shield configured to blocktransmission of stimulation energy to tissues external to the carotidsheath.